Digital-based medical devices

ABSTRACT

A skin measuring microscope includes a housing, an electronic imager disposed along an imaging axis, and an illumination system. The illumination system includes a plurality of LEDs disposed in a ring-like configuration adjacent a distal end of the housing.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a continuation of and claims priority under 35U.S.C. § 120 to U.S. patent application Ser. No. 15/589,173, filed onMay 8, 2017 and entitled: DIGITAL-BASED MEDICAL DEVICES, which is acontinuation of U.S. patent application Ser. No. 14/592,195 (now U.S.Pat. No. 9,642,517 B2), filed on Jan. 8, 2015 and entitled,“DIGITAL-BASED MEDICAL DEVICES”, which is a continuation of and claimspriority to U.S. patent application Ser. No. 13/673,822 (now U.S. Pat.No. 8,944,596 B2) filed on Nov. 9, 2012 and entitled, “DIGITAL-BASEDMEDICAL DEVICES”, which claims priority to U.S. Provisional ApplicationNo. 61/557,864, filed on Nov. 9, 2011 and entitled, “DIGITAL IMAGINGDEVICES AND METHODS OF USE”, the entire contents of which areincorporated herein by reference.

TECHNICAL FIELD

The application generally relates to the field of diagnostic medicineand more specifically to digitally based medical devices.

BACKGROUND

Numerous types of medical devices are presently known for the purpose ofconducting aspects of patient examinations. These devices can include,by way of example, an otoscope used for examining the ear, anophthalmoscope for examining the eye, a laryngoscope for examining thethroat, a skin measuring microscope for examining skin related defectsand conditions, and a colposcope for examining the cervix. Hand-heldversions of these devices include those manufactured and sold by WelchAllyn, Inc. of Skaneateles Falls, N.Y., among others. In opticalversions of these devices, such as an otoscope or ophthalmoscope, adiagnostic handle retains a set of standard or rechargeable batteries inwhich an instrument head is attached to the top of the handle, theinstrument head retaining the optics required to permit examination of atarget of interest. Digital versions have also been manufactured inregard to at least some of these devices.

Still further certain examinations, such as those involving the eye,have only been possible using a dedicated and much more complexapparatus, such as a fundus camera that is used for purposes ofconducting retinal imaging of the eye and further permitting thedetection of other maladies, such as diabetic retinopathy and maculardegeneration, given the field of view that is required and in which apatient is examined without having to administer eye drops in order todilate the pupil for purposes of conducting an examination.

It is a general and ongoing need in the field to develop improveddigitally based medical devices, including medical examinationinstruments.

SUMMARY

Therefore and according to one aspect, there is provided a hand heldophthalmic examination instrument comprising an illumination system forproviding illuminating light, the illumination system directing theilluminating light toward a target of interest. The illumination systemincludes a first light source emitting the illuminating light in anarrow wavelength range of between about 550 nm and about 600 nm, asecond light source for emitting a flash of white (broadband) light,wherein said illumination system directs both the illuminating light andthe flash of the white light toward the target of interest, and at leastone lens for directing light rays of the illuminating light and of theflash of white light in preselected directions toward the target ofinterest. The ophthalmic instrument further comprises an imaging systemfor directing the illuminating light as reflected from the target ofinterest to a viewing location, in which the imaging system includes: adigital imager at the viewing location for detecting and capturing adigital image of the target of interest, and a digital displayelectrically connected to the digital imager for displaying the captureddigital image of the target of interest. The ophthalmic instrumentfurther includes a memory for storing the captured digital image of thetarget of interest and a processor electrically connected to the memory,the illumination system, and the imaging system for controllingoperation thereof.

According to one version, the hand held ophthalmic instrument comprisesa converging lens for converging light rays of the illuminating lightand of the flash of white light toward an apex. In one embodiment, theapex is situated at or near a pupil of an eye.

According to another version, the imaging system further includes aplurality of lenses forward of said viewing location and centered on anoptical axis of the examination instrument, and wherein one of theplurality of lenses includes an optical focusing element capable ofvarying its thickness in response to an application of a focusingvoltage thereto. More specifically, the optical focusing element cancomprise a so-called “liquid lens”, wherein the instrument can includean automatic focus control capable of varying the focusing voltage untila focused image of the target of interest is captured by the imager. Atleast one or a plurality of such lenses can further provide a systemless prone to image jitter.

According to one version, the instrument includes a memory for storingat least two preset focusing voltages, wherein the at least two presetfocusing voltages are alternately applied to the focusing element undercontrol of the processor for alternating a focal length of the focusingelement corresponding to the at least two focusing voltages such thatthe digital display alternately displays the target of interest ascaptured at the at least two alternating focal lengths. According to yetanother version, the imaging system further includes a beam splitter fordirecting a portion of the illuminating light as reflected from thetarget of interest to a second viewing location, and a second digitalimager at the second viewing location for detecting and capturing asecond digital image of the target of interest. A second plurality oflenses is disposed forward of the second viewing location, wherein oneof said second plurality of lenses includes a second focusing elementcapable of varying its thickness in response to an application of asecond focusing voltage thereto, and wherein the digital display iselectrically connected to the second digital imager for displaying thesecond digital image on a portion of the digital display.

The instrument preferably further comprises a DC power source forproviding electric power to the illumination system and the imagingsystem. According to one version, the power source comprises at leastone of a rechargeable DC power source such as a battery. According toanother version, the rechargeable DC power source includes a supercapacitor or an ultra capacitor.

The first light source can include an LED, a laser diode, or anincandescent bulb. According to one version, the first light sourcecomprises means for varying the wavelength of light emitted by the firstlight source.

The second light source can according to at least one version, include aplurality of LEDs each separately illuminable and each emitting lighthaving a different wavelength than another one of the LEDs.Alternatively, the second light source can include at least one of awhite light LED, a white light laser diode, and a white lightincandescent bulb.

In a preferred version, the instrument further comprises a fixationlight source positioned at a preselected distance from the optical axissuch that when a person directly views the fixation light source, apreselected area of the person's retina is visible to the imagingsystem. In another version, a plurality of fixation light sources areeach positioned at a preselected distance from the optical axis, theplurality of fixation light sources arranged in a circular formation andeach illuminable individually such that when a person directly views anilluminated one of the fixation light sources a preselected area of theperson's retina, corresponding to a position in the circular formationof the illuminated one of the light sources, is visible to the imagingsystem.

The processor of the herein described instrument can comprise a programfor stitching together into one continuous digital image, thepreselected areas of the person's retina captured by the imaging system.

The digital display according to at least one version includes a sizeand location adjustable cursor box controlled by the processor inresponse to user input for selecting an area of the digital displaycorresponding to an area of the target of interest to be captured as adigital still image.

According to another version, the instrument can further comprise amicrophone connected to the processor for capturing an audible voicecommand, wherein the processor is programmed to initiate capturing adigital image of the target of interest in response to the voicecommand.

According to another version, the instrument comprises means forcontrolling a property of the light emitted by the first or the secondlight source. These means can comprise an aperture wheel or anadjustable iris for controlling a width of a beam of light emitted bythe first or the second light source. In another version, the widthcontrolling means can comprise at least one filter positioned forward ofthe first or the second light source for filtering the light emitted bythe first or the second light source. The at least one filter cancomprise, for example, a color filter or a polarizing filter.

In at least one version, the instrument includes a communicationinterface for connecting the processor to an external processing systemand for exchanging data between the processor and the externalprocessing system. An indicator can be provided on the instrument orotherwise for indicating that a data exchange is in progress and statusof the data transfer. The data exchanged between the processor and theexternal processing system can include software upgrades transmitted tothe instrument as well as captured digital images transmitted to theexternal processing system. The communication interface can be at leastone of a wireless communication interface or a wired communicationinterface. A wired communication interface can comprise at least one ofa USB interface, a PCI interface, an ePCI interface, and an Ethernetinterface. The wireless communication interface can comprise at leastone of an IEEE 802.11 interface, a cellular interface, or anotherwireless standard compliant interface.

According to yet another version, the ophthalmic instrument furthercomprises a patient interface including an eye cup for coupling theexamination instrument with the patient, and configured for contacting aregion of the patient's face surrounding an eye of the patient. The eyecup according to at least one version is fabricated from a flexiblematerial for conforming to the region of the patient's face surroundingthe eye of the patient and includes flexible ribs for flexiblyconforming to the region of the patient's face surrounding the eye ofthe patient. In a preferred version, the eye cup comprises an openingtherethrough, wherein a pupil of the eye of the patient can be viewedfrom a position external to the examination instrument. Using the above,a distance between the pupil of the eye and the converging lens and thewidth of the beam of light emitted by the first or the second lightsource are both adjusted such that a region of a retina of the eye thatis illuminated by the illuminating light comprises between about twentydegrees and about thirty five degrees.

According to yet another version, there is provided a method ofperforming an ophthalmic examination, the method comprising the stepsof: illuminating a target of interest using amber light comprising anarrow wavelength range of between about 550 nm and about 600 nm; andfollowing said step of illuminating, illuminating the target of interestusing white (broadband) light; and simultaneously with said step ofilluminating the target of interest using white light, capturing adigital still image of the target of interest.

According to at least one embodiment, the step of illuminating thetarget of interest using white light comprises the additional step ofemitting the white light for less than about one-tenth of a second.

In one version, the step of simultaneously capturing the digital stillimage comprises the step of using an electronic digital imager and inwhich the displayed image is illuminated by the amber light. In oneversion, the method further comprises the step of automatically focusingthe target of interest simultaneously with said step of illuminating thetarget of interest using the amber light. In one version, the latterstep comprises the additional step of adjusting a focal range of aliquid lens, which can be done, for example, by the additional step ofvarying a voltage applied to the liquid lens.

In one preferred version, the target of interest is an eye and whereinthe step of illuminating the target of interest using the amber lightcomprises the additional step of converging light rays of the amberlight at an apex at or near a pupil of the eye. In one embodiment, theilluminating step is performed using an LED that emits the amber light.In another version, the LED can be a white LED wherein an amber filteris positioned in front of the LED.

Similarly and according to one version, the step of illuminating thetarget of interest using the white light comprises the additional stepof activating an LED that emits the white light. In another embodiment aplurality of LEDs can be activated, emitting light of different colorsfor generating the white light.

In one embodiment, the step of capturing a digital still image of thetarget of interest comprises the additional step of adjusting a cursorbox on the digital display around a portion of the target of interest asilluminated by the amber light. In another version, the above step canbe carried out by detecting an audible command for electronicallytriggering the step of capturing the digital still image.

One advantage that is realized herein is that of enhanced imagingcapability that can be commonly imparted to a suite of medicalexamination instruments and other types of medical devices, includingmonitors. The introduction of at least one optical focusing element,such as at least one liquid lens assembly, enables dynamic focusingwhich accelerates the overall examination process and overall ease ofuse of the device design.

Another advantage is that a plurality of different medical devices caninterrelate with a common docking and charging station for purposes ofcharging and for data storage, retrieval and transmission.

Still another advantage is that an eye examination can be successfullyprovided with numerous features that have only previously been availablein larger and far more complex and costly fundus cameras. Enhanceddiagnostic capability is provided in a narrow (undilated) pupil.

Yet another advantage is that use of a variable focus lens assembly,such as a liquid lens, significantly reduces the incidence of imagejitter. Other features can also be provided, such as inclusion of atleast one positional sensor that simplifies the operation of the deviceand reduces the amount of direct user interaction.

Still another advantage is that of modularity of instruments, such as asuite of diagnostic or examination instruments is made possible.

These and other features and advantages will be readily apparent fromthe following Detailed Description, which should be read in conjunctionwith the accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is a partial side elevational view, taken in section, of anexemplary medical device in accordance with a first embodiment;

FIG. 1B is a partial schematic view of the illumination system of theexemplary medical device of FIG. 1A;

FIG. 1C depicts an enlarged view of an exemplary means for varyingaperture of light source of the medical device of FIG. 1B;

FIG. 1D is a front facing view of an LED die having multiple emitters;

FIG. 1E is a side view of the LED die of FIG. 1D;

FIG. 1F is a schematic view of the imaging system of the exemplarymedical device of FIG. 1A;

FIG. 2A depicts a side elevational view of a variable focus lensassembly in accordance as used in the medical device of FIG. 1A;

FIG. 2B depicts a single variable focus lens assembly;

FIG. 2C depicts a multiple variable focus lens assembly;

FIGS. 3A-3B depict a pixel binning method;

FIG. 3C depicts a schematic circuit diagram for selectively performing apixel binning method;

FIG. 4A depicts the engagement of the patient interface of the medicaldevice of FIG. 1A;

FIG. 4B is an enlarged view of a patient interface, including anobservation slot;

FIG. 5A is a top view, taken in section, of a medical device includingan aiming/fixation light;

FIG. 5B is a front facing view of a medical device including a circulararray of aiming/fixation lights;

FIG. 5C is the side elevational view of the medical device of FIG. 5B;

FIGS. 6A and 6B are schematic views of the optical system of a medicaldevice illustrating a field of view control for reducing a distancebetween a patient's eye and the diagnostic instrument for increasing afield of view of the patient's retina;

FIG. 7 is an front perspective view of a chin rest assembly made inaccordance with an exemplary embodiment for use with the medical deviceof FIG. 1A;

FIG. 8 depicts an exemplary docking station for a medical device;

FIG. 9 depicts a generic schematic diagram of medical devices inaccordance with the present invention;

FIG. 10 is a rear perspective view of another medical device having aperipheral device releasably incorporated therewith;

FIG. 11 is a schematic view of a configuration of the optical systemwithin the medical device of FIG. 10 , relative to an electronic imagerof an attached peripheral device;

FIG. 12 is a front perspective view of a medical device in accordancewith another exemplary embodiment;

FIG. 13 is a side perspective view of the medical device of FIG. 12 ;

FIG. 14 is a rear perspective view of the medical device of FIGS. 12 and13 ;

FIG. 15 is a side elevational view, taken in section of the medicaldevice of FIGS. 11-14 ;

FIG. 16 is an enlarged sectioned view of a portion of the medical deviceof FIG. 15 ;

FIG. 17 is a front perspective view of a medical device in accordancewith another exemplary embodiment;

FIG. 18 is a rear perspective view of the medical device of FIG. 17alongside a second type of medical device;

FIG. 19 is a side elevational view of the medical devices depicted inFIG. 18 ;

FIG. 20 is a rear perspective view of a portion of a medical device madein accordance with another exemplary embodiment;

FIG. 21 is a front perspective view of the medical device of FIG. 20 ;

FIG. 22 is a side elevational view, taken in section, of the medicaldevice of FIGS. 20 and 21 ;

FIG. 23 is an enlarged section view of the medical device of FIGS. 20-22;

FIG. 24 is a rear perspective view of a medical device made inaccordance with another exemplary embodiment and as mounted in a testfixture;

FIG. 25 is a side sectioned elevational view of the medical device ofFIG. 24 , as depicted within the test fixture; and

FIG. 26 is an enlarged portion of the sectioned view of the medicaldevice of FIG. 25 .

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

The following discussion includes numerous exemplary embodiments ofmedical devices, and more specifically medical examination instrumentsthat permit digitized images of a medical target of interest to becaptured, whether displayed locally at the instrument and/or remotelyfor purposes of examination. In order to provide a suitable frame ofreference in regard to the accompanying drawings, certain terms are usedthroughout this description. These terms, such as “lateral”, “above”,“below”, “distal”, “proximal”, “top”, “bottom”, “upper, “lower”,“inner”, “outer” and the like are not intended to narrow the scope ofthe herein described invention as further defined in accordance with theclaims, except where so specifically indicated.

In spite of the numerous examples provided herein, it should be readilyapparent that many other variations and modifications can becontemplated by one of sufficient skill, including but not limited toalternatives involving the specific instrument and overall functionalityas well as attendant features.

As used herein, the terms “medical diagnostic device or “medicalinstrument” and “medical examination device or instrument” are usedinterchangeably and pertain to a medical field instrument, such as butnot limited to an otoscope, an ophthalmoscope, a skin microscope, anendoscope, a colposcope, a rhinoscope, a laryngoscope, an anoscope andthe like in which diagnostic or examination data can be obtained throughimagery of the patient. The concepts as related herein are intended tobe applicable to any such device, including but not limited to monitors.

As used herein, the term “electronic imager” refers to an electroniccharge coupled device (CCD) array, a CMOS photodiode array or similardevices that can be used to capture a digital image.

As used herein, the term “imaging” refers to capturing a digital imageof a target of interest using the electronic imager.

As used herein, the term “optical focusing element” can refer to avariable focus lens assembly, such as at least one liquid lens assemblywherein a thickness of the lens varies, and thereby its focal plane,according to a voltage level applied thereto.

As used herein, the term “illuminating system” refers to light sourcesand components to direct light beams therefrom to illuminate a target ofinterest.

As used herein, the term “primary axis” refers to the center axis of thehousing extending through each of the distal and proximal ends of themedical device.

As used herein, the term “processor” refers to a general purposeprocessor, an embedded processor, or controller coupled to a digitalmemory system comprising instructions retrieved and executed by theprocessor for controlling operation of all electronic components of themedical diagnostic instrument in response to user inputs received fromuser interface input means and from data received from the electroniccomponents that indicate status of the components.

As to the discussion that follows, a generic medical device is firstdiscussed prior to descriptions of more specific exemplary deviceembodiments. In general and first referring to FIG. 9 , a generalizedschematic diagram of a medical device is herein described. First, themedical device 1000 includes a housing 1004 fabricated from commonmetallic alloys or thermoplastic resins and defined by an interior 1008,which is appropriately sized to retain a number of components or inwhich the housing 1004 is configured to receive a peripheral device,shown in phantom as 1090 and as discussed infra. The housing 1004 issuitably shaped for portable use, wherein the housing 1004 can includean integral handle 1012 according to at least version in order tofacilitate single-handed operation.

The housing 1004 is defined by a distal end 1016 that retains a patientinterface (shown schematically as 1020) and an opposing proximal end1024. The patient interface 1020 can be integrated with the housing 1004or separably attached thereto, as discussed in the various exemplaryembodiments which follow, and in which the interface directly contactsan area of a patient in at least one version. As noted, the handle 1012extending from the lower portion of the housing 1004 enables the device1000 to be compactly held and operated using only a single hand of auser (not shown) and can further retain a portable power supply 1018, asdiscussed herein, although other portable configurations, with orwithout handles, are possible.

The portable power supply 1018 can include at least one standard batterysuch as a lithium-ion battery or a rechargeable battery. As described inU.S. Pat. No. 9,153,994, entitled Motion Sensitive and Capacitor PoweredHandheld Device, issued Oct. 6, 2015, and U.S. Pat. No. 8,890,489,entitled Capacitive Power Supply for Handheld Device, issued Nov. 18,2014, which are hereby incorporated herein by reference in theirentireties, power supplies comprising high energy density capacitors,e.g. super capacitors or ultra-capacitors, may be utilized as the powersupply in the medical diagnostic imaging instrument 10. Such powersupplies allow fast charging times sufficient to store enough electricalenergy to power the instrument for several hours and therefore canenable limited numbers of operation with a very short charge time, or ahybrid combination of the above battery types can be provided.

An optical system 1030 (shown in phantom) is retained within theinterior of the housing 1004 and includes a plurality of opticalcomponents or elements commonly aligned along an imaging axis 1040 ofthe device 1000 in order to permit an image of a target of interest 1044to be suitably directed onto an electronic imager 1050, such as a CCD, aCMOS or other suitable component. According to this embodiment, theimaging axis 1040 is coincident with the primary axis of the medicaldevice 1000 although this positioning can be suitably altered, asdiscussed infra.

The overall constituency of the optical elements that are provided inthe optical system 1030 will obviously vary between types of medicaldevices including various examination instruments, as discussed hereinfor purposes of acquiring a suitable image of the intended target ofinterest 1044. In addition, the optical system 1030 can further includea focusing mechanism in which at least one optical element or the imager1050 is moved in relation to each other. According to at least oneversion, at least one optical focusing element, such as at least oneliquid lens assembly, is arranged along the imaging axis 1030 of thedevice 1000 and as further discussed in subsequent embodiments. Theaddition of the latter assembly enables dynamic “on the fly” focusingautomatically with no moving parts and in which jitter is effectivelyreduced.

The device can also include an illumination system 1060 that comprisesat least one light source 1066 capable of producing adequate light alonga defined illumination axis 1070 of the device 1000 towards the targetof interest and to enable imaging by the electronic imager 1050. In atleast one version, the illumination system further provides means toallowing aiming the instrument for purposes of imaging a specificmedical target of interest, as discussed herein, such as portions of theeye.

The light source 1066 can be an incandescent bulb, an LED, a laserdiode, or other suitable source that, along with aligned illuminationoptics produces an adequate beam of light incident on the target ofinterest. According to at least one embodiment, this source 1066 can besuitably be configured as discussed herein to provide varyingwavelengths of light to the target to provide standard, spectral,polarization and/or other forms of digital imaging depending on theapplication (examination) being performed. In one version, the lightsource can comprise an array of LEDs, including infrared and nearinfrared. In another version, at least one filter and/or polarizationelement can be provided in conjunction with either the imaging and/orillumination systems of the device 1000 to alter the wavelength ofemitted light and/or to reduce the incidence of glare. According toanother version, the illumination system can be optional, for example,when using IR detection such s from the skin of a subject.

The medical device 1000 further includes a display 1072, which,according to one version, is integrated with the instrument housing 1004and connected to a processor 1076 for purposes of processing imagestaken by the electronic imager 1050 for presentation. Preferably, thedisplay 1072 can be aligned with the primary axis of the device 1000 toprovide a compact and convenient overall design, although other suitablearrangements can also be utilized and as illustrated herein. In anotherversion, the display itself can also be optional in the instance inwhich the electronic imager 1050 and processor combine to simply captureand store a plurality of images for later transmission to a remote site.

A user interface (UI) 1080 to enable operation, as needed, includes atleast one actuable element 1084, such as a button or switch, disposed onthe housing 1004 and interconnected to the processor 1076. In thecurrent embodiment, the user interface 1080 is provided along one sideof the handle 1012 of the device 1000, but could also be disposed, forexample at or near the display 1072. In an effort to reduce the overallcomplexity of the UI 1080 and also to minimize the risk of image jittercaused by user interaction, at least one positional sensor 1086 can bedisposed on or proximate the housing 1004 to provide a signal that istransmitted to the contained processor 1076. For example, the positionalsensor 1086 can comprise at least one accelerometer, such as athree-axis accelerometer. In one embodiment, the accelerometer candetect and produce a signal when the housing 1004 is being picked up, aswould be the case in actual use or in the instance in which a signal hasnot been detected for a predetermined time interval indicative ofinactivity. In the former example, the signal from the accelerometercauses the device 1000 to automatically power up while the latter cancause the instrument to assume a dormant or “sleep” mode of operation.According to yet another example, the positional sensor 1086 cancomprise an attitude sensor, such as a gyroscopic sensor, that sensesazimuthal or other positional changes in the instrument housing 1004.According to yet another example, a signal can be produced by a userthat can be detected by the positional sensor 1086, such as by tappingone side of the display 1072, which can be indicative of either a leftor a right image being taken by the medical device 1000.

According to another version, and also to prevent unnecessary movement avoice command feature can be provided. A microphone 15 (FIG. 1A) builtinto the instrument housing 29 detects the voice of the operator of theinstrument. A voice recognition program stored in the processor 24 cantherefore control certain features of operation, and avoiding theoveruse of user actuated controls. According to one embodiment, the useof voice commands can control the exposure step for imager 20.Advantageously, the voice command image capture step avoids therequirement that an operator press a button or otherwise make physicalcontact with the medical diagnostic imaging instrument 10, therebyavoiding unnecessary movement of the instrument during digital imagecapture.

As discussed herein according to at least one other version, theelectronic imager 1050, display 1072, processor 1076 (or at leastportions thereof) and optionally at least a portion of the illuminationsystem 1060 can be separately defined within a peripheral device 1090,such as a smart phone, a tablet computer, an iPad or any other suitablecompact device that includes a portable camera, which is releasablyattached to the housing 1004 and in which the electronic imager of theperipheral device is aligned with the imaging axis of the device 1000.Application software that is resident within the peripheral device 1090enables use of same with the medical device 1000 in which enhancedcapabilities of the peripheral device 1090 itself creates versatility,as well as additional processing power. In terms of the smart phone, forexample, the optical system 1030 of the device 1000 can be augmentedsuch that the imaging axis 1040 is aligned with the electronic imager(not shown) of the attached peripheral device 1090, while enabling theperipheral device to be disposed substantially along the primary axis ofthe device 1000, providing compactness of design but without impactingfunctionality.

Otherwise and in a dedicated device 1000, the processor 1076 can bearranged within the housing 1004 and connected to the electronic imager1050, the display 1070 and the illumination system 1060, the processor1076 having resident software for operating the medical device 1000based on inputs from the user interface 1080 and embedded instructions.The retained power source 1018 can be recharged using a docking station,shown schematically as 1094, configured to receive at least one saidmedical device 1000 and in which data transfer can also be initiatedeither automatically through attachment or selectively using wired orwireless transmission means (arrows 1096, 1097). The docking station1094 can also be configured to serve as a recharging port for thecontained power supply. Another example of a station is shown in FIG. 8and described in greater detail below.

Advantageously, the present invention provides a medical device thatutilizes an electrically controllable focusing system that is simple,compact, provides the desired dynamic range, has few moving parts,consumes a minimum of electrical power, and can be incorporated intoexisting instrument designs. With the preceding generic description, thefollowing embodiments present certain embodiments that are specific tovarious exemplary medical examination instruments and more specificallyophthalmoscopes, otoscopes, skin measuring microscopes and colposcopes.It will be understood, however, based on the above generic descriptionthat the concepts discussed herein are equally applicable to othermedical devices, such as but not limited to endoscopes, retinoscopes,rhinoscopes, larygnoscopes, anoscopes, and the like.

An ophthalmic instrument is herein next described. Referring first toFIGS. 1A-1D and more specifically to FIG. 1A, a cross-sectional view isprovided of the ophthalmic instrument 10 having an illumination system11 and an imaging system 12. FIG. 1B is a schematic diagram, shown inisolation, of the illumination system 11 of the instrument 10. FIG. 1Fis a schematic diagram, shown in isolation, of the imaging system 12 ofthe instrument 10 for use in illuminating and forming an image of atarget such as a portion of a patient's eye, for example, the retina.With regard to the illumination system 11, there are included separatelycontrollable light sources 30, 31, a condensing lens 32 and a mirror 34each disposed along a defined illumination axis 35. The light sources30, 31 can be any generic light source, such as a filament based lamp, ametal halide lamp, a Xenon lamp, the end face of a fiber optic cable, alaser diode, or a single or multiple LED array.

In one embodiment, the light sources 30, 31 comprise single or multipleLED elements which can be illuminated individually or simultaneously.Exemplary LED light sources comprise a source of white light such as anRGB LED having wavelengths of the red (R), the green (G), and the Blue(B) colors of the white spectrum. In one embodiment, the light sources30, 31 comprise a filter 33, such as an infrared filter for permittinglight wavelengths of about 780-820 nm to pass therethrough or an amberfilter to permit light wavelengths of about 580-610 nm to passtherethrough for reasons discussed herein. Either or both light sources30, 31 may include a filter positioned forward (i.e., distal) of thelight source. Light sources 30, 31 further comprise aperture wheels 21,25, respectively, to direct light, represented by light cones 26, 27,respectively, along an illumination axis 35. An example of amechanically operable aperture wheel is illustrated in FIG. 1C, whereinapertures of various sizes can be rotated into an aligned positionforward of light sources 30, 31 and along the illumination axis 35. Asmaller aperture size allows less light to pass therethrough but thelight is constrained into a narrower beam. A larger aperture size can beused to allow more light along the illumination path such as, forexample, if a larger region of a retina is to be illuminated.Alternatively, other means for varying the amount of incident light canbe utilized; for example, an adjustable iris (not shown).

A condenser lens 32, centered on the illumination axis 35, convergeslight from the light sources 30, 31 onto the mirror 34, which reflectsthe illuminating light along an imaging axis 22 to an objective lens 14,which causes the light to converge at an apex 39 at or near the cornea23 of a patient's eye 36 and diverges inside the eye 36 of the patientto illuminate a wide area of the retina 38. Light can be selectivelyemitted from the second light source 30, under control of a processor 42using a contained power supply 13, and reflected off a beam splitter 41disposed along the illumination axis 35 through the converging lens 32to the mirror 34. Light emitted from the light source 31 travels throughthe beam splitter 41 along illumination axis 35 through the converginglens 32 to the mirror 34, which reflects the illuminating light parallelto the imaging axis 22 to the objective lens 14, as before.

Imaging system 12 includes at least one objective lens 14 (which alsoforms part of the illumination system), an imaging lens 16, a variablefocus liquid lens assembly 18, and an electronic imager 20 each spacedand aligned along the imaging axis 22. The lens assembly 18 iscontrolled by the contained processor 42 using a variable voltagecontrol 24 or other suitable means. The electronic imager 20 maycomprise any known image sensor, such as a CCD or CMOS imager. Duringexamination of a patient, the imaging axis 22 is approximatelycoincident with the optical axis of a patient's pupil 23. In allreferences herein, the terms “lens” and “lens assembly” can refer to asingle optical element or a plurality of optical elements functioningtogether. Light reflected from the retina 38 of a subject is transmittedalong the imaging axis 22 by the objective lens 14, through an imageplane 28, the focusing lens assembly 18 and the imaging lens 16 to theelectronic imager 20. The imager 20 produces an electronic (digital)image, which is displayed on display 40 after the signal has beenprocessed by the processor 42. The processor 42 can be programmed tocontrol the electronic imager 20 during exposure and to capture andstore image data generated by and received from the imager 20. Theprocessor 42 can execute autofocus software wherein an image displayedon the display 40 is automatically focused through a lens voltagecontrol 24 and the focusing lens assembly 18.

The processor 42 detects the image state of focus and drives voltage tothe liquid lens 18 to obtain the sharpest image. The response time ofthe processor 42 in transmitting voltage control signals to the focusinglens assembly is sufficiently rapid to reduce, to a certain extent,shaking or jitter effects during image capture, and so serves tosignificantly minimize the incidence of jitter. As described herein, theprocessor 42 is disposed within the confines of the instrument housing29, but could alternatively be located external to the instrument 10. Iflocated externally, the processor 42 can communicate with the imager 20either through wired or wireless communication channels (not shown inthis embodiment). The components of the instrument 10 are preferablycontained in the housing 29 that can be maintained by gripping a handleportion thereof and in which the instrument is configured for singlehanded operation. Alternatively, the components of the instrument 10 canbe contained in a housing fixedly supported on a table, floor or othersurface.

As shown in FIG. 1F, the image of a portion of the eye reflected alongthe imaging axis 22 is transmitted using the optical components of theimaging system 12 to the electronic imager 20, which is alsoappropriately aligned (i.e., centered) on the imaging axis 22. Thedisplay 40 can be suitably positioned for viewing by the user. In oneversion, the display 40 can be aligned along the imaging axis 22 such ason the housing 29, or alternatively, the display can be disposed awayfrom the imaging axis 22 such as shown in FIG. 18 , wherein the displayscreen 3090A is positioned off of, and above, the imaging axis 22. Theelectronic imager 20 produces an electronic image for display on thedisplay 40 and can be viewed in real time thereon by the caregiver.

FIG. 2A is a diagrammatic view of a preferred variable focus liquid lens18 that is incorporated within the imaging system 12 of the hereindescribed ophthalmic instrument 10 and aligned along the imaging axis22. As shown and according to this exemplary embodiment, the variablefocus liquid lens assembly 18 includes a housing 61 that incorporates apair of parallel transparent windows 62 and 63, a first electrode 64having a frusto-conical opening 65, an insulating layer 66 disposed onthe first electrode 64, a second electrode 67, an insulator 68, a dropof insulating liquid 69 located on the conical insulating layer 66 andon the window 63, and an electrically conductive liquid 70 filling theremainder of the housing 61. The filled conductive liquid 70 is inelectrical contact with the second electrode 67 while the insulatingliquid 69 and the conductive liquid 70 are in contact along a meniscusregion represented by solid line 71. The insulating liquid 69 andconductive liquid 70 are both transparent, are immiscible, havedifferent optical indexes, and have substantially the same density.Conductive liquid 69 can, for example, be water mixed with salts andinsulative liquid 70 can be oil. In one embodiment, the lens assembly 18includes one or more electrically controllable variable focus liquidlenses. As shown in FIG. 2B, the lens assembly 18 includes one variablefocus liquid lens 50, or, as shown in FIG. 2C, the focusing lensassembly 18 may alternatively include first and second spaced variablefocus liquid lenses 51 and 52 with a controllable variable iris 54located between the lenses 51 and 52. The variable iris 54 controls theamount of light passing through the liquid lens assembly 18 comprisingmultiple liquid lenses 51, 52.

In operation and when no voltage is applied, the system is said to be atrest. In this configuration, the drop of insulating liquid 69 naturallytakes the shape of the solid line designated by reference curve 71. Anaxis 72 is perpendicular to the window 62 and passes through the centerof the curve 71. At rest, the drop of insulating liquid 69 is centeredabout an axis 72, which is perpendicular to the window 62 and passesthrough the center of the reference curve 71. This latter axis 72constitutes the optical axis of the lens.

Applying a non-zero voltage V from the variable voltage control 24between the first electrode 64 and the second electrode 67 creates anelectrical field localized in the region surrounding the electrodes. Asa consequence, the conductive liquid 70 deforms the insulating liquiddrop 69 and the reference curve 71 resultantly assumes the shapedesignated by the dashed line 74. This results in a variation of thefocal length of the liquid lens. A range of applied voltages will resultin a range of various radii of curvature for the dashed line 74 andtherefore, a corresponding range of optical powers and focal lengths forthe liquid lens.

One embodiment of an ophthalmoscope comprising the liquid lens 18, asdescribed above, includes use of the liquid lens in assisting to alignthe imaging axis of the ophthalmoscope with a pupil of the patient.Under control of a caregiver who operates a toggle switch, or initiatesa toggle function, in the ophthalmoscope's user interface, the liquidlens 18 can be switched between at least two focal lengths while thecaregiver aligns the ophthalmoscope with the patient's pupil. One of thefocal lengths is preselected for an overall view of the patient's eye(distal focal length) so that the caregiver can determine the spatialorientation of the ophthalmoscope as the caregiver advances theophthalmoscope toward the patient's eye. Another of the preselectedfocal lengths comprises a standard, or caregiver preferred, focal length(near field focal length) used for examining a portion of the eye of thepatient. Because the focal length of the liquid lens is controlled bythe voltage applied thereto, as explained above, each preselected focallength corresponds to an applied voltage level, which level can bestored in memory as voltage level data to be accessed by theophthalmoscope processor when the toggle function is selected by thecaregiver. The voltage levels as applied are alternated according to thevoltage level data which rapidly adjusts the liquid lens' focal length.The digital images generated as between the two focal lengths can bealternately displayed on the display 40 as the liquid lens is toggledand the ophthalmoscope is moved into position for examining an eye ofthe patient. The speed at which the toggle switch alternates betweenviews may be preset, or controlled by the caregiver.

Another useful application of the toggling function includes a splitscreen display, or a picture-in-picture display, to simultaneouslydisplay the images as generated by the two preselected focal lengths. Inthe present ophthalmic embodiment in which one imager is used, one ofthe toggled images can be captured and displayed as a still image whilethe other image is simultaneously displayed as a live motion image.Thus, the toggling function serves to alternate between displaying oneof the near field or distal focal length image as a digital still imagewhile the other is displayed in live motion, and vice versa. In anophthalmic or other embodiment using two imagers, each imager canindependently and simultaneously transmit live motion images to besimultaneously displayed on display screen 40 as split screen orpicture-in-picture live motion images. In this embodiment, the imagersmay each implement a liquid lens assembly 18, in which each assembly isset at a different one of the preselected focal lengths so that the nearfield and distal focal length live motion images are simultaneouslydisplayed on display screen 40. To generate two parallel imaging axesfor the two imager embodiment herein described, a beam splitter can bedisposed in the optical axis of the ophthalmoscope, or alternatively acollimation lens together with two mirrors can be used to generateparallel imaging axes each directed to one of the imagers. It should benoted that the foregoing arrangements are equally applicable in otherinstrument designs as used for other applications.

Light sources 30, 31 may be fitted with a filter 33 for providing lightat selected wavelengths, depending on the filter that is utilized. Forexample, an infrared filter or an amber colored filter may beimplemented as desired. In the present ophthalmic embodiment, an ambercolor filter 33 is utilized to provide illuminating light for observinga portion of an eye of a patient without causing an undue reaction inthe patient due to light sensitivity, such as constriction of the pupil.The use of this filter therefore allows greater visibility of interiorregions of the eye, such as the retina, without requiring dilation usingeye drops, which is highly advantageous. Light in the amber wavelengthrange of about 590 nm allows the pupil to remain open while allowing acaregiver to observe desired interior portions of the eye. The caregivercan opt to capture a digital still image of the portion of the eye beingexamined, as desired. At the moment that a desired portion of the eye isin view on the display, the still digital image capture procedure may beinitiated by manual or voice command, as described herein, under controlof the processor 42 wherein a broadband white light source, such asprovided by the light sources 30, 31 can be flashed and a digital imageof the desired portion of the eye is captured while the eye is soilluminated. In this example, it may be preferable to modify the lightsource 30 to emit an amber wavelength light while the light source 31 ismodified to emit white light. In another embodiment, the light sourcescomprise LEDs, without filters, whose emission spectra comprise desiredwavelengths or illuminating light such as RGB LEDs for providing whitelight, and appropriately doped LEDs for generating amber colored light,for example. Such an arrangement of LEDs is shown in FIGS. 1D-1E whereina width of each of the LEDs is about 1 mm or less. In yet anotherembodiment, the imager 20 may be sufficiently sensitive, or anenvironment, wherein an examination is taking place using the ophthalmicinstrument 10, may provide sufficient natural light, to capture digitalimages without requiring an activation of illumination system 11. Forexample, if imager 20 is designed for detecting and capturing thermalimages, then illumination system 11 may not require activation duringimage capture. In fact and in this latter example, the use of anillumination system can be made optional since infrared signals from amedical target would not require the incidence of light.

In another embodiment, each of the herein described light sources 30 and31 can comprise a plurality of multi-color light sources, such asmultiple LEDs, each emitting a different wavelength of light. Such LEDlight sources may be separately illuminable in order to provideilluminating light of various colors. Similar to the description abovefor using an amber colored light to illuminate a portion of an eye, andprior to capturing a digital image thereof, the multi-color lightsources can be used to capture multiple digital images of a body partunder various illumination conditions, such as illumination under lighthaving different wavelengths. A series of exposures can be programmed tooccur in a short duration with each exposure occurring underilluminating light having a different wavelength under programmedcontrol of processor 42. Each exposure may be programmed to occur underseveral capture settings. For example, one or more exposures can each beprogrammed to be associated with a particular color of illuminatinglight, f-stop, exposure speed, and diopter setting. Each combination ofsettings be programmed to occur upon each exposure such that the eye (orother medical target) can be imaged under various illuminations and atvarious depths using optimal light conditions known to enable idealimage detail. For example and regarding a captured image of a relevantportion of the eye, the ratio of diameters of artery (A) to vein (V)provides useful information relating to hypertension.

FIG. 3A illustrates a portion of the electronic imager 20 comprising aplurality of photodetectors (pixels) in the form of photodiodes forcapturing image data. Each pixel comprises an image area for capturinglight energy of a certain wavelength, e.g., green (G), red (R), and blue(B). The density of pixels arranged in an area of the imager 20determines the resolution of the imager 20. The amount of light energycaptured by each pixel determines a brightness of the captured image,while the resolution of pixels determines the sharpness of the image. Atradeoff occurs between brightness and sharpness of a captured digitalimage because the smaller the pixel size (area), the greater the digitalimage's resolution and the lower its brightness. Binning is a process(i.e., an algorithm) that can be designed to take advantage of thesepixel properties, as desired. For example and under low lightconditions, it may be preferable to increase an amount of brightnesscaptured by the imager 20 even though resolution may be decreasedthereby. In another example, if an electronic display screen, such asdisplay screen 40 (or display screen 3090 of FIG. 14 , or 3090A of FIG.17-19 , or 4080 of FIG. 20 ) is not capable of displaying a highresolution digital image, then the resolution can be decreased during animage capture step because it will not incur a cost as far as resolutiondisplay is concerned. As represented in the schematic circuit of FIG.3C, each pixel 301 of the imager 20 transmits image capture data to animage processor during full resolution processing of captured imagedata. In this processing mode, maximum digital image resolution isobtained and can be displayed on an electronic image display havingsufficient resolution. In a second mode of operation, all the pixels inthe imager 20 are logically grouped into four adjacent pixels each 302and are selectively connected to a summer circuit 304, under processorcontrol, wherein the combined light energy captured by each group offour adjacent pixels is summed together. The sum is used to representthe value of a virtual quad-pixel 302, as shown in FIG. 3B, having aboutfour times the size of one pixel in full resolution mode. This virtualquad-pixel captures more total light energy for increased brightness,but generates one-fourth the resolution as compared to a full resolutionmode. Each group of four adjacent pixels consists of two green pixels,one red pixel, and one blue pixel, as defined by the familiar Bayerpattern utilized in many commercial image sensor arrays. The processormay be programmed to switch between full resolution mode and anincreased brightness mode, as desired. Using this algorithm, more lightenergy is captured in each quad-pixel to represent one of a plurality ofvirtual re-sized imager pixels, thereby increasing overall visible imagebrightness, albeit with lower resolution, after processing.

With reference to FIG. 4 , there is illustrated an eyecup portion 401 ofthe herein described ophthalmic instrument. According to thisembodiment, the eyecup portion 401 may made of biodegradable and/orrecyclable material or may be made from a biodegradable material ortreatable with an additive, if made from polyethylene and polypropylene,such as Green Solutions PPI BD-0301 or Oxo-Degrader, among others, thatdegrades the interface within a prescribed time period. The eyecupportion 401 is modified to include a slot 402 that is angularly providedrelative to a primary axis of the eyecup portion to permit a caregiverto observe a location of the patient's pupil with respect to theilluminating light emitted by the ophthalmoscope 10. By observing apatient's eye through the eyecup slot 402, the caregiver can positionthe illuminating light emitted by ophthalmoscope 10 so that theilluminating light is properly directed to a portion of the eye desiredfor viewing by the caregiver. After the caregiver confirms that theilluminating light is directed at the correct portion of the eye, suchas the pupil, the caregiver can be assured that the image appearing onthe display is correct and thereafter orient the ophthalmoscope usingthe display.

During examination of a patient's eye, it is often desired to have thepatient's gaze directed at an angle so that portions of the patient'seye can be made visible to the caregiver for examination. Such aprocedure can be made effective if the patient is provided a target uponwhich to fix his or her gaze. With reference to FIG. 5A, there isillustrated a top view cross-section of the medical diagnostic imagingdevice 10. In the present ophthalmic embodiment, the instrument 10 isprovided with at least two LEDs 501, 502 that are selectivelyilluminated for providing a point upon which a patient undergoing anophthalmic examination can fix their gaze. For example, if the userdesires to obtain a view of the patient's optic disk, it is known thatthe optic disk is ideally visible through a pupil of the eye if the eyeis fixed at a viewing angle 503 that is approximately 16 degrees inward504, as measured from a line of sight 505 fixed directly forward. Thus,the LED 501 is illuminated for the patient to fixate his or her gazewhile the optic disk in the patient's left eye is being examined, andthe LED 502 is illuminated for the patient to fixate his or her gazewhile the optic disk in the patient's right eye is being examined(illustrated in FIG. 4A). The LEDs 501, 502 can be electricallyconnected to the power supply and each can be manually switched on bythe user using external controls provided on the ophthalmoscope 10.

In another embodiment, a plurality of LEDs can be positioned forward ofthe objective lens 14, as illustrated in FIGS. 5B-5C, in order toprovide a range of fixation angles for the patient. As shown and using aplurality of individually illuminable LEDs e.g., 506, 507 that arearranged along a circular die 508, a series of digital images can becaptured of portions of the eye, e.g., through the undilated pupil,having different regions exposed for viewing with each fixation point.In one embodiment, the multiple LEDs can be replaced with multipleoptical fibers, or multiple bundles of optical fibers, illuminated byLEDs or other light sources in a handle or other portion of theophthalmoscope.

In one embodiment, a series of digital images of the retina can becaptured each at a different viewing angle through an undilated pupilwhile the patient fixates on a different one of the illuminated LEDspositioned in the circular arrangement. The series of retinal digitalimages can then be stitched together as a single continuous digitalimage of the patient's retina. Using conventional digital imagestitching algorithms, a larger field of view of the patient's retina canbe generated for optimal examination using this technique.

With reference to FIGS. 6A-6B, there is illustrated an arrangement ofoptical components that allows examination of a larger region of apatient's retina 38. Two adjustments of optical components can be madeto enable an illuminated field of view 603 of the patient's retinacovering approximately 20 degrees that can be increased to a field ofview 604 of approximately 35 degrees. First, the objective lens 14 ispositioned closer to the patient's eye, from a first distance 601 ofabout 35 mm to a second distance 602 of about 20-21 mm. This positioningallows light rays converging at an apex 39 to enter the interior of apatient's eye 36 at a wider angle, and thereby allowing a greater region604 of the retina 38 to be illuminated. Together with this adjustment,the aperture 21 and/or 25 of the light source 30 and/or 31,respectively, is increased by approximately 30-35%, such as by rotatingaperture wheel 21, 25 (FIG. 1C) to position a larger aperture forward ofthe light source, or by adjusting a variable iris to increase itsaperture, to allow a wider beam of light to pass through the aperture 21and/or 25, through condensing lens 32 eventually passing through theobjective lens 14 that is converged at the apex 39. The wider field ofview of retina 38 improves a diagnostician's ability to perceivecharacteristics of the retina, which may indicate types of retinopathyassociated with, for example, diabetes or detection of glaucoma.Similarly, a wider dispersal of light rays reflected by the patient'sretina allows an image of the wider field of view to be captured forlater examination or for archival purposes.

In order to capture clear images during a medical examinations using ahand held medical diagnostic imaging instrument as described herein, itis typically preferred to utilize means for avoiding instrument orpatient movement during a digital image capture step or during a digitalimage capture sequence. Any such movement can cause obvious blurring ofdigital images and less obvious decreased sharpness of captured digitalimages. One means for avoiding unnecessary movement of the instrumentand/or the patient is by the use of a chin rest that can receive theinstrument and enable proper placement and fixation of the patient. Oneembodiment of a chin rest is illustrated in FIG. 7 , wherein chin restportion is formed for receiving a patient's chin in resting contact witha portion 702. A separate spaced portion 701 is formed forsimultaneously receiving a patient's forehead in contact therewith.Having the patient rest his or her head in this manner in the chin rest700 allows the patient's head to be secured without movement.Simultaneously, the handle portion of the diagnostic imaging instrument10 is inserted into portion 703 of the chin rest 700, which securelyfixes the diagnostic instrument in place without movement or shaking.The instrument can then be rotated along a horizontal plane controlledby rotation of a base portion 705, and can also be vertically raised orlowered using handle 704. A bottom portion of chin rest 700 can befitted with a surface for providing friction, such as rubber contacts orthe like or alternatively, the assembly may be fitted with means forimmovably attaching the chin rest 700 to a table top or other surface.The bottom portion 706 of the chin rest 700 may be made of a densematerial for increasing an overall weight of the chin rest, therebyadding inertia that helps to prevent movement of the chin rest duringuse.

A second feature that is helpful to avoid unnecessary movement of thediagnostic imaging instrument is use of voice commands to trigger asingle image capture or an image capture sequence. A microphone 15 (FIG.1A) built into the instrument housing 29 detects the voice of theoperator of the instrument. A voice recognition program stored in theprocessor 24 can therefore control certain features of operation, andavoiding the overuse of user actuated controls. According to oneembodiment, the use of voice commands can control the exposure step forimager 20. Advantageously, the voice command image capture step avoidsthe requirement that an operator press a button or otherwise makephysical contact with the medical diagnostic imaging instrument 10,thereby avoiding unnecessary movement of the instrument during digitalimage capture.

Referring to FIG. 8 , there is illustrated a charging and datacommunication station 801 comprising a receptacle 803 for receiving andsupporting a handle 44 of the hand held instrument 10. Charging and datacommunication station 801 includes a power cable 807 for connecting thestation 801 to an electrical power source, and a communication cable 805for connecting the station 801 to a processing system (not shown), suchas a PC, laptop, server, or a hand held processing system device. Asillustrated herein, communication cable 805 comprises a USBcommunication cable, but may comprise any of several communicationcables, such as a PCI cable, an Ethernet cable, or an ePCI cable, forconnecting the station 801 to processing system such as a PC, laptop,server, or other hand held processing system device such as a smartphone or tablet computer. Contained within housing 804 of the station801 are charging and data control electronics 806 for selectivelycontrolling a charging function and a data transfer function of chargingand data communication station 801. A bottom of the handle 44 of theinstrument 10 may comprise a mating connector for completing a matingconnection with the station 801 terminal 802 whereby two way datatransfers between the medical diagnostic imaging instrument 10 and aprocessing system connected via communication cable 805 can take place.Such data transfers can include digital images captured and stored inthe instrument 10 being transferred to the connected processing system,and software upgrades for use by the processor 42 of the hand heldmedical diagnostic imaging instrument 10 transferred from the connectedprocessing system. Such data transfers can take place with or withoutpower cable 807 being connected to a power source such as provided, forexample, in a USB compliant communication cable. If the power cable 807is connected to a power source a charging current controlled byelectronics 806 will supply voltage at a stepped down voltage asnecessary to fully charge the imaging instrument 10. Alternatively, ifthe hand held medical diagnostic instrument 10 comprises a wireless datacommunication capability, the data transfers described above can takeplace without use of terminal 802 of data communication station 801.

Referring to FIGS. 10 and 11 , another exemplary embodiment of a medicaldevice 2000 is herein described. The medical device 2000 depictedaccording to this exemplary embodiment is an ophthalmoscope, althoughthe specific type of instrument can be varied as discussed herein. Morespecifically, the medical examination instrument 2000 is defined by ahousing 2004 having a distal end 2006, a proximal end 2007, a handle2010 and an interior 2008 (partially shown in FIG. 11 ) that isappropriately sized to retain, among other features, an optical system2030 and an illumination system (not shown), each similar to those shownin FIGS. 1A and 1B. A patient interface 2050 in the form of an eye cupis releasably attached to the distal end 2006 of the housing 2004.According to this version and rather than integrating certain componentswithin the instrument housing 2004, each of the electronic imager,processor and display are commonly provided within a peripheral device2060 that is releasably attached to the proximal end 2007 of the housing2004 and more specifically within a defined receptacle 2062. Accordingto this specific embodiment, the peripheral device 2060 that is attachedto the instrument housing 2004 is a smart phone. Alternatively, however,other devices could also be utilized, such as a tablet computer and/oran iPad or other device that includes an embedded portable camera.Referring to FIG. 11 , the receptacle 2062 according to this embodimentis defined by an open ended cavity 2064 having an outer wall 2066 thatis open with the exception of a lateral retaining edge 2068 enabling thedisplay 2070 of the peripheral device 2060 to be visible therethrough aswell as permitting access to various control features of the peripheraldevice 2060.

In addition and as depicted in FIG. 11 , the contained electronic imager2084 of the peripheral device 2060 may not be centrally located. In thisinstance and in order to provide an efficient and compact overallassemblage, the optical system 2030 of the instrument 2000 can be offsetfrom the primary or center axis 2014 of the device 2000 using at leastone mirror or lens 2094 so as to fold the imaging axis 2036 away fromthe primary axis 2014 of the housing 2004 so as to provide opticalalignment with the electronic imager 2084 of a retained peripheraldevice 2060.

In use, the additional processing power of the attached peripheraldevice 2060 provides synergies in regard to the herein described device2000. The receptacle 2062 provides an effective mechanical and opticalinterface and in which images are transmitted wirelessly to the “cloud”or a dedicated IT infrastructure. Application software in the peripheraldevice 2060 enables the medical device 2000 to be operated using theuser interface of the device or using the touch screen and controls ofthe peripheral device 2060.

Referring to FIGS. 12-16 , another exemplary medical device isdescribed. According to this version, the medical device is a digitalotoscopic instrument. As in the preceding generic and ophthalmicversions previously discussed, the otoscopic instrument 3000 is definedby an instrument housing 3004 that includes an interior 3008 sized forretaining a plurality of components, as well as a handle 3012 thatpreferably enables a user to operate the instrument 3000 using a singlehand.

The otoscope housing 3004 is further defined by a distal end 3016 and anopposing proximal end 3020, the former including a substantiallyfrusto-conical distal insertion portion 3024 that is configured toenable the releasable attachment of a speculum tip element 3030, whichis used as the patient interface for the foregoing instrument 3000. Thespeculum tip element 3030 is preferably a disposable molded plasticcomponent that is defined by a frusto-conical configuration and whichincludes a hollow interior having open distal and proximal ends 3034,3038. In use, the tip element 3030 is shaped to be releasably placed inoverlaying relation onto the exterior of the distal insertion portion3024. The tip element 3030 can be made from plastic materials that arerecyclable. According to at least one version, the tip element 3030 canbe made from a material that is biodegradable or treatable, aspreviously discussed, such that degradation occurs within a prescribedtime period.

The speculum tip element 3030 further includes engagement features thatpermit releasable attachment including a set of circumferentiallydisposed ribs 3037 that are formed at the proximal end 3038 of thespeculum tip element 3030 for engagement into a set of receiving slots3044 that are provided on a retainer member 3040 of the instrument 3000adjacent the distal insertion portion 3024. The retainer member 3040includes a rotatable actuating knob 3046 disposed over the exterior ofthe retainer member 3040 wherein the speculum tip element 3030 is placedinto engagement by aligning the proximal end 3038 of the tip element3030 with the retaining member 3040 and twisting the tip element 3030such that the ribs 3037 are moved into the slots 3044. Rotation of theactuating knob 3046 against a spring bias (not shown) causes an interiorfeature (not shown) of the knob 3046 to push the ribs 3044 from thereceiving slots 3044 of the retainer member 3040 and the speculum tipelement 3030 from the housing 3004. Further details relating to theattachment mechanism and the engagement features of the speculum tipelement are provided in commonly owned U.S. Pat. Nos. 7,399,275 and8,066,634, the entire contents of each herein being incorporated byreference.

The distal insertion portion 3024 of the herein described medicalexamination instrument 3000 includes a distal tip opening 3026 such thatwhen attached to the insertion portion 3024, the open distal ends 3026,3034 of the distal insertion portion 3024 and the speculum tip element3030 are respectively aligned with one another along an imaging axis3045 of the instrument 3000.

An imaging system 3050 disposed within the housing 3004 comprises aplurality of optical components that are linearly disposed along theimaging axis 3045, which according to this version is also coincidentwith the primary or center axis of the instrument 3000. These opticalcomponents include an objective lens doublet 3054 that is disposed atthe distal end 3026 of the distal insertion portion 3024, as well as aset of intermediate relay lenses 3056 and an aperture stop, each fixedlydisposed within a series of lens tubes that are axially interconnectedwith one another within the housing 3004. An additional relay lens 3058is disposed adjacent the electronic imager 3087 as well as an objectivedoublet 3060 maintained by an air gap therebetween, the latter elementsbeing separately retained within a separate enclosure. As discussedaccording to FIGS. 2A-2D and 9 , a variable lens focus assembly such asa liquid lens, can be disposed in the optical train.

According to one version, the initial focal point can be set manually,or automatically, to focus on the tympanic membrane of the middle ear tocapture an image of the membrane. Thereafter, in quick succession andunder processor control, the focal point can be incrementally adjustedby shifting one or more diopters to a focal plane above or beyond thetympanic membrane and an image captured thereof using a preselectedilluminating light, f-stop, etc., as explained above, that optimallyilluminates portions of the ear canal beyond the tympanic membrane, suchas near infrared light.

An illumination system 3070 includes at least one light source 3074,which according to this embodiment is an incandescent bulb that isdisposed adjacent the exterior of the housing 3004 in relation to thepolished proximal end of a plurality of optical fibers (not shown) thatfurther extend into the housing 3004 including distal ends (not shown)that are configured circumferentially about the interior of the distalopening 3026 of the distal insertion portion 3024 so as to project lightto be directed through the speculum tip element 3030 and toward thetarget of interest.

Other alternative configurations regarding the type and placement oflight sources are intended herein. For example and in lieu of anincandescent bulb, a ring-like configuration of LEDs can be disposed atthe distal end of the insertion portion 3024, the LEDs being maintainedat the distal periphery of the insertion portion 3024 between the opticsand the interior wall of the insertion portion. This particularconfiguration is advantageous in that the LEDs provide sufficientillumination and further act to prevent condensation/fogging of theoptical system, particularly the distally placed objective lens 1054, atthe time of examination. This arrangement further assists significantlywith heat dissipation. By providing a plurality of LEDs, the amount ofillumination of each LED can be controlled using a rheostat or similarfunction with the additional option of selecting specific LEDS at anyone time. For example, in a ringlet of 8 LEDS, only 4 center disposedLEDS could be used in accordance with one embodiment depending on theapplication. In another version, the LEDs can emit light of differentwavelengths relative to each other.

According to this latter embodiment, the speculum tip element 3030 isfabricated from an optically clear and biocompatible material, such aspolyethylene or polypropylene, and in which the application of lightfrom the LED ring causes conduction of light throughout the entirespeculum tip element 3030 due to the optically clear nature thereof.According to one version, the tip element can be treated with anadditive, such as Green Solutions PPI-BD-0301 or Oxo-Degrader, enablingbiodegradability after a prescribed time period.

An electronic imager 3087 is aligned with the imaging axis 3045 at theproximal end 3020 of the housing 3004 according to this embodiment, theimager 3087 being configured to capture at least one digital image of atarget of interest. According to this version, the electronic imager3087 is a CCD or CMOS imaging element. The optical system directs theimage of the target of interest to the imager 3087, which is arranged ona printed circuit board, and which according to this embodiment furthersupports a processor (not shown) connected therewith. The positioning ofthe objective lens 3054 and the aligned optical components furthercreates a distal entrance pupil that prevents vignetting while alsopermitting a field of view in which the entire tympanic membrane can beviewed all at once when the speculum tip element is placed within theear of a patient (not shown). Additional details regarding the opticalsystem, including the distal entrance pupil is provided in U.S. Pat. No.7,399,275, the entire contents of which are herein incorporated byreference.

A display 3090 is electrically connected to the electronic imager 3087according to this exemplary embodiment by means of a flexible circuit3091 attached to the printed circuit board and in which according tothis embodiment, the display 3090 is also aligned along the primary axisof the instrument 3000 and mechanically and electrically integrated intothe proximal end 3020 of the housing 3004. Alternative positioning ofthis latter component, however, is possible as is shown according toFIGS. 17-19 , which depict medical examination instruments 3000A, eachhaving integrated displays 3090A that are disposed above the remainderof the housing 3004A. Other suitable configurations are possible.

The processor is electrically interconnected to each of the foregoingcomponents in order to receive, store and transmit images captured bythe electronic imager 3087, as well as operate the instrument 3000 usinga user interface 3095 which is provided on the handle 3012 as shown inFIG. 15 or alternatively at the proximal end 3020 of the housing 3004adjacent the display, as depicted in FIG. 14 . The user interface 3095includes at least one user actuable control member 3096. These memberscan permit capture, review of images captured, deletion of images, aswell as those for powering the device. Relative axial movement betweenthe electronic imager 3087 and at least one of the optical elements3058, 3060 enables focusing of the herein described instrument 3000.Alternatively, a variable focus lens assembly, as discussed at FIGS. 2Aand 2B, can be disposed within the defined optical train and enabledynamic on the fly focusing automatically. In addition and in connectionwith same, the focus position of the at least one liquid lens can besuitably adjusted by one or more diopters on either side of a nominalfocus position such that the depth of focus can be selectively changed.The foregoing feature enables the target of interest to be adjusted, forexample, to permit viewing the tympanic membrane and other areas withinthe ear for detection of infection (i.e., otitis media) when usingdifferent spectral light sources in which subsurface effects can readilydetected. The use of spectral imaging for observing subsurfaces of atargeted body part is described in U.S. Pat. No. 9,001,326, entitledMethod and Apparatus for Observing Subsurfaces of a Target Material,issued Apr. 7, 2015, which is hereby incorporated by reference in itsentirety.

The herein described otoscope 3000 is powered directly through acontained portable power supply, such as at least one rechargeablebattery or the inclusion of a super capacitor, such as previouslydescribed and preferably retained within a defined cavity in the handle3012. Though the present embodiment relates to the inclusion of allrelated components on or within the housing 3004, it will be readilyunderstood that the electronic imager, processor (or at least a portionof the functionality thereof) and display can alternatively be providedin a separate peripheral device such as a smart phone or a tabletcomputer that can be releasably attached to the housing 3004, and aspreviously described with reference to FIGS. 10 and 11 .

The herein examination instrument 3000 can further be used, for example,with the docking stations such as those depicted in FIGS. 8 and 9 inorder to enable charging of the contained portable power supply, as wellas to facilitate data/image transfer to a remote device or station.

Referring to FIGS. 20-23 , a skin measuring microscope device orinstrument version is herein described in accordance with an exemplaryembodiment. As in the preceding versions described herein, the skinmeasuring microscope 4000 of this embodiment comprises an instrumenthousing 4004, as well as a handle 4008 extending from a lower portion ofthe housing 4004 to preferably enable the instrument 4000 forsingle-handed operation. The handle 4008 further includes a definedinterior that retains a compact power source 4012, which can include aset of rechargeable batteries or alternatively can include a supercapacitor, as previously discussed. The remainder of the instrumenthousing 4004 also includes an interior 4014 that is configured and sizedto retain a plurality of components, which according to this embodimentinclude an optical system 4020, an electronic imager 4050, a processor,an illumination system and a display 4080, each of the foregoing beingintegral to the housing 4004 or disposed in relation thereto.

The optical system 4020 comprises a plurality of optical componentsincluding a first lens 4024, a second lens 4027 and an aperture plate4028 disposed between the first and second lenses that combine to forman air gap objective doublet and aligned optically with the electronicimager 4050 along an imaging axis 4026. The optical system according tothis embodiment is configured to provide optimal focus based on an imageplane formed at the distal end of a flexible patient interface and uponcompression thereof onto the skin surface (not shown) of a patient. Theelectronic imager 4050, which is supported on a printed circuit board aswell as the processor (not shown), is also aligned with the optical axis4026 of the instrument 4000 and interconnected via the processor to thedisplay 4080, which according to this specific embodiment is integrallymounted to an opposing proximal end 4007 of the housing 4004. Otherarrangements such as those shown in FIGS. 17-19 can also be utilized.

The illumination system includes at least one light source whichaccording to the present embodiment includes a plurality of LEDs 4044,such as white LEDs, that are arranged in a ring-like configuration atthe distal end 4006 of the instrument housing 4004 and adjacent thepatient interface 4060. At least one filter (not shown) can be includedrelative to the light source.

The flexible patient interface 4060 is configured to make contact withthe skin of the patient (not shown) and according to a preferredversion, is separably attached to the distal end 4006 of the instrumenthousing 4004. According to another version, the patient interface 4060is made from a material, such as polyethylene or polypropylene or othersuitable material or combination of suitable materials, that enablerecyclability and reuse. The patient interface 4060 according to thisembodiment is a cylindrical section that extends distally from theinstrument housing 4004 when attached as shown herein and wherein theflexible nature of the interface 4060 permits limited compression ofsame when in engagement with a skin surface for examination.

A user interface 4090 is formed on the exterior of the handle 4008 ofthe instrument housing 4004, including at least one user-actuableelement 4092, such as a button or switch that enables control of atleast one operational feature of the herein described instrument 4000.Alternative arrangements to simplify the number of controls required bythis interface, such as previously described, should be readily apparentincluding but not limited to voice control, use of positional sensorsand the like. According to the herein described embodiment, each of theforegoing components (i.e., illumination system, electronic imager,display) are integrated within the housing 4004 and are electricallycoupled to the processor. Alternatively, the electronic imager, displayand processor (or at least certain functional aspects thereof) can beseparately provided in a peripheral device (not shown) that can beattached and configured relative to the optical system and theprocessor, as previously described and shown in FIGS. 10 and 11 .

In operation and according to this embodiment, the patient interface4060 can be secured as a disposable component that is separate from theremainder of the assembly and which is placed in releasable fashion ontothe distal end of the instrument housing 4004. Alternatively, thepatient interface can already be provided on the housing either as areleasable or as an integral component. In terms of disposability, theinterface can be made from a material that is biodegradable or can betreated with an additive that permits biodegradability after apredetermined time period. The handle 4012 of the instrument 4000 isgripped and the attached flexible patient interface 4060 is placed intointimate contact against the skin of the patient (not shown). Pressureis applied so as to compress the flexible patient interface to form alight seal and wherein the optics within the housing 4004 are preferablyarranged to provide optimal focus based on axial compression of thepatient interface 4060. The instrument 4000 is enabled using the userinterface 4090, which activates the electronic imager 4050, theprocessor 4070, the LED array 4044 and the display 4080. The light thatis emitted by the LED array 4044 is directed at the skin area ofinterest and images can be viewed on the display 4080 and subsequentlycaptured and stored. According to at least one version, variouscharacteristics of skin-related conditions can be measured in which theprocessor can include resident software that is configured to measure atleast one characteristic of the skin-related condition (color, edgeirregularity (shape), size, etc.) and compares at least onecharacteristic to stored thresholds. In addition, the processor caninclude memory that permits later images of the same area of skin to bere-measured and compared for changes to a condition of interest (e.g.,scar, mole, wart, lesion, etc.) using the same measurement scales orfiducial marks or by comparing prior and current images.

Recharging of the contained portable power supply 4012 for the hereindescribed medical examination instrument 4000 can be performed using adocking station, similar to that previously discussed herein and shownin FIGS. 8 and 9 . The docking station may include at least one dataport that permits image data transfer from the instrument when docked.An indicator (not shown) on the instrument housing 4004 is illuminatedto indicate the state of data transfer. Alternatively, data can bedirectly transferred from the herein described instrument 4000 usingwired and/or wireless transmission means. For example, the hereindescribed instrument handle can include a USB or similar data portaccording to an alternative version or can include a wireless antenna totransfer data and to receive status changes to operating software and/oroperating protocol, as needed.

According to another version and in lieu of a handle, the instrumenthousing can assume a tubular, substantially cylindrical or similar shapeand in which the user can directly grip the exterior of the instrument.According to this design, the skin measuring microscope is similar inappearance to that of a loupe, but without an eyepiece; that is, anelectronic imager and display are used in lieu of an eyepiece. Theportable power supply according to this version is also disposed withinthe interior of the housing.

Referring to FIGS. 24-26 , there is shown a colposcopic version of amedical examination instrument that is made in accordance with yetanother exemplary embodiment. Reference is made herein to U.S. Pat. Nos.6,359,677 and 6,147,705, incorporated by reference in their entiretythat relate to the general aspects of an electronic colposcope. As inthe preceding versions described herein, the colposcope 5000 is definedby a housing 5004 (partially shown in this embodiment) having aninterior 5008 that is configured to retain a plurality of components,including an illumination system 5030, an optical system 5020, anelectronic imager 5050, a processor (not shown), a portable power supply(not shown) and a display 5060, each of which are retained or areintegral to the housing 5004 (only partially shown) according to thisembodiment. Further details relating to the housing and support ofexemplary colposcopic instruments are provided in the above crossreferenced patents.

The colposcope housing 5004 further includes a distal end 5006, as wellas an opposing proximal end 5007 in which the housing 5004 andillumination system 5030 are each supportably mounted within a fixture5040 having a test frame 5044 and in which target (i.e., a femalecervix) is simulated herein by a separately and adjacently supportedmember 5048 disposed a predetermined working distance from theinstrument housing 5004 and illumination system 5030.

According to this embodiment, the interior 5008 of the colposcopehousing 5004 retains the optical system 5020, which includes a pluralityof optical elements linearly disposed along an optical axis 5044 andfurther aligned with the electronic imager 5050 which is disposed in theproximal end of the housing 5004, the latter being maintained on aprinted circuit board along with the processor (not shown). Theillumination system 5030 is provided adjacent the housing 5004 andincludes at least one coupled light source such as an arc lamp or otherconvenient source capable of producing sufficient illumination.

In use, illumination is directed along a defined illumination axis atthe target of interest and in which reflected light from the target isdirected along the optical axis 5044 to the imager 5087 disposed withinthe housing 5004 for viewing at the display 5060 as well as for capture.Filtering can be provided either in hardware or software, such as agreen filter, to aid in cervical examinations.

Alternatively, a peripheral device (not shown) having an integratedelectronic imager, display and processor could be separately attached inreleasable fashion to the housing 5004 and wherein the electronic imageris aligned with the optical axis of the instrument 5000. An exemplaryversion of this concept is previously discussed herein and shown atFIGS. 10 and 11 .

PARTS LIST FOR FIGS. 1-26

-   10 instrument-   11 illumination system-   12 imaging system-   13 power supply-   14 objective lens-   16 imaging lens-   18 focusing lens assembly (variable focus liquid lens assembly)-   20 imager-   21 aperture wheel-   22 imaging axis-   23 pupil-   24 variable voltage control (lens voltage control)-   25 aperture wheel-   26 light cone-   27 light cone-   28 apex-   29 housing-   30 light source-   31 light source-   32 condensing lens-   33 filter-   34 mirror-   35 illumination axis-   36 eye-   38 retina-   40 display (display screen)-   41 beam splitter-   42 processor-   50 liquid lens-   51 lens, variable focus liquid-   52 lens, variable focus liquid-   54 variable iris-   61 housing-   62 transparent window-   63 transparent window-   64 first electrode-   65 frusto-conical opening-   66 conical insulating layer-   67 second electrode-   68 insulator-   69 insulating liquid (liquid drop)-   70 insulating liquid-   71 reference curve-   72 axis-   74 dashed line-   301 LED-   302 LED-   401 eyecup portion-   402 slot, eyecup-   1000 medical device-   1004 housing-   1008 interior-   1012 handle-   1016 distal end-   1018 power supply, portable-   1020 proximal end-   1030 optical system-   1034 optical components-   1040 imaging axis-   1050 electronic imager-   1060 illumination system-   1066 light source-   1070 illumination axis-   1072 display-   1076 processor-   1080 user interface (UI)-   1084 actuable element-   1086 positional sensor-   1090 peripheral device-   1094 docking station-   1096 arrow-   1097 arrow-   2000 medical device-   2004 housing-   2006 distal end-   2007 proximal end-   2008 interior-   2010 handle-   2014 primary or center axis-   2030 optical system-   2036 imaging axis-   2050 patient interface-   2060 peripheral device-   2062 receptacle-   2064 open ended cavity-   2066 outer wall-   2068 lateral retaining edge-   2070 display-   2084 electronic imager-   2094 folding mirror or lens-   3000 medical examination instrument-   3004 housing-   3008 interior-   3012 handle-   3016 distal end-   3020 proximal end-   3024 distal insertion portion-   3026 distal opening, insertion portion-   3030 speculum tip element-   3034 distal tip opening-   3037 ribs, tip element-   3038 proximal tip opening-   3040 retaining member-   3044 receiving slots-   3045 imaging axis-   3046 actuating knob-   3050 optical system-   3054 objective doublet-   3058 relay lens-   3060 objective doublet-   3070 illumination system-   3074 light source-   3087 electronic imager-   3089 flexible circuit-   3090 display-   3095 user interface-   3096 control member-   4000 medical instrument-   4004 housing-   4006 distal end-   4007 proximal end-   4008 handle-   4014 interior, housing-   4020 optical system-   4024 objective lens element-   4026 optical axis-   4050 electronic imager-   4060 patient interface-   4080 display-   4090 user interface-   4092 actuable control member-   5000 medical instrument-   5004 housing-   5006 distal end-   5007 proximal end-   5008 interior-   5012 portable power supply-   5020 optical system-   5030 illumination system-   5040 test fixture-   5044 frame-   5048 simulated target-   5050 electronic imager-   5060 display-   5070 processor

The invention claimed is:
 1. A skin measuring microscope comprising: ahousing; an optical system comprising a plurality of optical componentsaligned along an imaging axis, said plurality of optical componentsincluding a first lens, a second lens and an aperture plate disposedbetween the first and second lens; an illumination system comprising aplurality of LEDs formed in a ringlet at a distal end of the housing; anelectronic imager aligned along the imaging axis; a display connected tothe electronic imager, enabling viewing of a skin area of interest; anda patient interface disposed at the distal end of the housing configuredfor contacting the skin area of interest, the patient interface beingconfigured for limited compression against the skin area of interestwherein an image plane of the optical system is formed relative to adistal end of the patient interface, such that the limited compressionof the patient interface creates a light lock for the illuminationsystem, as well as an optimal focus for the optical system for viewingthe skin area of interest.
 2. The skin measuring microscope as recitedin claim 1, in which the compressible patient interface is releasablysecured to the housing.
 3. The skin measuring microscope as recited inclaim 1, in which the compressible patient interface is at least one ofdisposable and recyclable.
 4. The skin measuring microscope as recitedin claim 1, in which the display is disposed at a proximal end of thehousing and substantially aligned along the imaging axis.
 5. The skinmeasuring microscope as recited in claim 4, in which the display isintegral to the housing.
 6. The skin measuring microscope as recited inclaim 1, in which the display is integral to the housing and is notaligned with the imaging axis.
 7. The skin measuring microscope asrecited in claim 1, further comprising a processor connected to theelectronic imager, the processor being configured to process and storeimages received from the electronic imager.
 8. The skin measuringmicroscope as recited in claim 7, in which the microscope is configuredto transfer at least one stored image on the processor to a remote site.9. The skin measuring microscope as recited in claim 8, furthercomprising a docking station sized and configured to receive themicroscope, wherein the docking station is adapted to receive image datafrom the microscope.
 10. The skin measuring microscope as recited inclaim 9, wherein the image data is transferred to the docking stationautomatically upon connection of the microscope to the docking station.11. The skin measuring microscope as recited in claim 7, wherein theprocessor is programmed to measure and scale at least one aspect of askin surface under examination.
 12. The skin measuring microscope asrecited in claim 7, further comprising at least one positional sensordisposed relative to the housing and coupled to the processor, whereindetection of signals from the at least one positional sensor are used bythe processor for controlling at least one feature of the microscope.13. The skin measuring microscope as recited in claim 12, in which theat least one feature includes powering of the skin measuring microscope.14. The skin measuring microscope as recited in claim 1, furthercomprising at least one feature that dissipates heat generated by theringlet of LEDs.
 15. The skin measuring microscope as recited in claim1, further comprising a user interface, including at least one useractuable element, for operating the microscope.
 16. The skin measuringmicroscope as recited in claim 15, in which the user interface includesat least one feature to control the amount of light emitted by theringlet of LEDs.
 17. The skin measuring microscope as recited in claim1, further comprising at least one filter movable into at least one ofthe imaging axis and an illumination axis of the illumination system.